EP0693948B1 - Lubricious catheters - Google Patents
Lubricious catheters Download PDFInfo
- Publication number
- EP0693948B1 EP0693948B1 EP94916763A EP94916763A EP0693948B1 EP 0693948 B1 EP0693948 B1 EP 0693948B1 EP 94916763 A EP94916763 A EP 94916763A EP 94916763 A EP94916763 A EP 94916763A EP 0693948 B1 EP0693948 B1 EP 0693948B1
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- EP
- European Patent Office
- Prior art keywords
- catheter
- catheter according
- distal
- segment
- proximal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/08—Materials for coatings
- A61L29/085—Macromolecular materials
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/14—Materials characterised by their function or physical properties, e.g. lubricating compositions
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/0045—Catheters; Hollow probes characterised by structural features multi-layered, e.g. coated
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/0045—Catheters; Hollow probes characterised by structural features multi-layered, e.g. coated
- A61M2025/0046—Coatings for improving slidability
Definitions
- This invention is in the general field of surgical instruments. It relates specifically to catheters which may be used in cardiovascular and endovascular procedures to deliver diagnostic, therapeutic, or vaso-occlusive agents or devices to a target site within a human or animal body which is accessible by a system of natural passageways within that body.
- the catheters are coated in such a way that they are exceptionally slippery and the coating is very durable.
- Catheters are increasingly used to deliver diagnostic or therapeutic agents and devices to internal target sites that can be accessed through the circulatory or other system.
- a torqueable guidewire is introduced into the vasculature and, using radiography to monitor its advance through the body's passageways, is rotated to allow the guidewire's bent guide tip to follow a chosen route (when a choice of pathways is found) and advanced towards the target site.
- the catheter is slid along the guidewire until the distal end of the catheter approaches the distal end of the guidewire. This procedure is repeated until the distal end of the catheter is positioned at the target site.
- a second technique for advancing a catheter to a target site is to use the blood flow as the motive force in placing the distal end of the catheter at the desired target site.
- Such methods often employ a highly flexible catheter having an inflatable, but pre-punctured balloon at its distal end.
- the balloon is partially inflated, and carried by blood flow into the target site.
- the balloon is continually inflated to replenish fluid leaking from the balloon.
- This technique too, has drawbacks including the fact that at least the distal portion of the catheter is so floppy that it cannot be pushed without buckling. Instead the catheter must be advanced using injected fluid to inflate the balloon to propel the catheter to the target site. Additionally, there is a risk of rupture of a vessel by a balloon that has been overinflated.
- over-the-wire catheters having variable stiffness are comparatively quite slow in time of access. Friction with the interior of the guide catheter or the vessel path considerably slows the procedure time.
- the over-the-wire catheters can be directed to portions of the vasculature inaccessible to the flow-directed catheter. Lowering the resistance of the over-the-wire catheter to improve its lubricity and allow improved access time to remote body sites forms a further aspect of this invention.
- This invention is generically a coated catheter having portions of differing flexibility which is suitable for the delivery of diagnostic, therapeutic, or vaso-occlusive agents or devices to potentially remote portions of the vascular system or other systems of open lumen within the body.
- the coating is significantly slipperier than other known coatings and is very durable.
- This invention also includes a method of coating catheters using lubricious hydrophilic polymers and a method for producing a thin layer of such polymers on polymeric substrates.
- US 4876126 refers to a medical instrument that has, on its surface, a reactive functional group which is covalently bonded with a water-soluble polymer. A large number of different polymers are described in columns 4 and 6.
- EP-A-0389632 refers to a slippery medical material and a process for its production. This material has surfaces possessing low frictional properties, allegedly provided by a large number of different materials mentioned on pages 4 to 12.
- US 5171232 on whose disclosure is based the preamble of claim 1, refers to a flexible plastic catheter, but there is no mention of a lubricious coating.
- the present invention relates to a catheter assembly comprising an elongated tubular (102, 402) member having proximal and distal (104, 106, 404, 406) ends and an inner lumen (108) extending between these ends, the member comprising:
- This coated catheter is suitable for placement within a tortuous, small vessel pathway and a method for delivery of an agent or device to a target site.
- the coating is very slippery and quite durable.
- the catheter may be directed to the target site either by means of the blood flow to that site or by the use of a guidewire.
- the catheter has an elongate tubular body having proximal and distal ends and a lumen extending between the ends through which the diagnostic, therapeutic, or vaso-occlusive agent or device is delivered. Where appropriate, the lumen may be used for passage of a guidewire.
- the elongate tubular body typically is formed of (a) a relatively stiff and, perhaps, tapered proximal segment, (b) a relatively flexible distal segment, and (c) a transition or intermediate section between the proximal and distal segments that is less flexible than the distal segment but more flexible than the proximal segment. At least the distal segment and, desirably, the transition segment of the catheter is treated with a lubricious, polymeric material. If so desired , all but the portion of the proximal section actually handled by the physician during final manipulation may be coated with the lubricious polymers.
- the catheter bodies are coated with hydrophilic polymeric materials by a method involving application of the polymer from a dilute polymer or oligomer solution followed by simultaneous solvent removal and curing of the applied precursor. Multiple coatings of the polymeric material are contemplated.
- FIG. 1 is a diagram that shows an infusion catheter constructed according to a preferred embodiment of the present invention.
- FIG. 2 is a diagram that shows the distal end on one embodiment of a flow-directed infusion catheter of the present invention in which the distal end is formed in an "S" shaped configuration.
- FIG. 3 is a diagram showing a flow-directed infusion catheter, stylet, and guiding catheter assembly.
- FIG. 4 is a side view of a typical catheter assembly according to this invention adapted for use with a guidewire.
- This invention is a catheter, optionally including a guidewire, having discrete sections of varying flexibility.
- the catheter has a relatively stiff proximal section and a less stiff mid portion.
- the distal end section is quite flexible; for devices intended for use with guidewires, the distal end section need not be quite as flexible since it need only follow the path of the guidewire without substantial disturbance of that pre-determined path.
- At least the distal portion of the catheter is coated with a polymeric material to increase its lubricity and to minimize the potential for trauma as it moves through the body lumen.
- the mid or transition section of the catheter may also be coated with the polymeric material.
- the proximal section may also be coated although most desirably a small proximal end portion is left uncoated for increased control.
- Particularly suitable as coatings in the catheter assembly of this invention are polymers or oligomers of monomers selected from N-vinylpyrrolidone; polyethylene glycol acrylates such as mono-alkoxy polyethylene glycol mono(meth) acrylates, including mono-methoxy triethylene glycol mono (meth) acrylate, mono-methoxy tetraethylene glycol mono (meth) acrylate, polyethylene glycol mono (meth) acrylate; acrylamide; acrylamidomethylpropane sulfonic acid and its salts. These monomers may be formed into homopolymers or block or random copolymers. The use of oligomers of these monomers in coating the catheter for further polymerization is also an alternative.
- Preferred monomers include N-vinylpyrrolidone; acrylamide polymerized into random or block copolymers.
- hydrophobic monomers may be included in the coating polymeric material in an amount up to about 30% by weight of the resulting copolymer so long as the hydrophilic nature of the resulting copolymer is not substantially compromised.
- Suitable monomers include ethylene, propylene, styrene, styrene derivatives, alkylmethacrylates, vinylchloride, vinylidenechloride, methacrylonitrile, and vinyl acetate.
- Preferred, because of their propensity for ease of linkage to the typical polymeric catheter substrates, are ethylene, propylene, styrene, and styrene derivatives.
- Polymers or oligomers applied using the procedure described below are activated or functionalized with photoactive or radiation-active groups to permit reaction of the polymers or oligomers with the underlying polymeric surface.
- Suitable activation groups include benzophenone, thioxanthone, and the like; acetophenone and its derivatives specified as: where
- the polymeric coating may then be linked with the substrate using known and appropriate techniques selected on the basis of the chosen activators, e.g., by ultraviolet light, heat, or ionizing radiation.
- Crosslinking with the listed polymers or oligomers may be accomplished by use of peroxides or azo compounds such as acetyl peroxide, cumyl peroxide, propionyl peroxide, benzoyl peroxide, or the like.
- a polyfunctional monomer such as divinylbenzene, ethylene glycol dimethacrylate, trimethylolpropane, pentaerythritol di- (or tri- or tetra-) methacrylate, diethylene glycol, or polyethylene glycol dimethacrylate, and similar multifunctional monomers capable of linking the polymers and oligomers discussed above is also appropriate for this invention.
- the polymeric coating may be applied to the catheter body or other polymeric substrate by any of a variety of methods, e.g., by spraying a solution or suspension of the polymers or of oligomers of the monomers onto the catheter or by dipping the catheter into the solution or suspension (after sealing the open ends, if so desired). Initiators may be included in the solution or applied in a separate step.
- the catheter may be sequentially or simultaneously dried to remove solvent after application of the polymer or oligomer to the polymeric body and crosslinked.
- the solution or suspension should be very dilute since only a very thin layer of polymer is to be applied.
- Preferred solvents for this procedure when using the preferred polymers and procedure are water, low molecular weight alcohols, and ethers, especially methanol, propanol, isopropanol, ethanol, and their mixtures.
- water miscible solvents e.g., tetrahydrofuran, methylene dichloride, methylethylketone, dimethylacetate, ethyl acetate, etc.
- tetrahydrofuran methylene dichloride
- methylethylketone dimethylacetate
- ethyl acetate etc.
- catheter bodies particularly preferred as a coating for the catheter bodies discussed below are physical mixtures of homo-oligomers of polyvinylpyrrolidone and polyacrylamide.
- the catheter bodies,or substrates are preferably sprayed or dipped, dried, and irradiated to produce a polymerized and crosslinked polymeric skin of the noted oligomers.
- the lubricious hydrophilic coating is preferably produced using generally simultaneous solvent removal and crosslinking operations.
- the coating is applied at a rate allowing "sheeting" of the solution, e.g., formation of a visibly smooth layer without "runs".
- the optimum coating rates are found at a linear removal rate between 0.25 and 2.0 inches/sec, preferably 0.5 and 1.0 inches/sec.
- the solvent evaporation operations may be conducted using a heating chamber suitable for maintaining the surface at a temperature between 25°C and the glass transition temperature (T g ) of the underlying substrate.
- Preferred temperatures are 50°C to 125°C.
- Most preferred for the noted and preferred solvent systems is the range of 75° to 110°C.
- Ultraviolet light sources may be used to crosslink the polymer precursors onto the substrate. Movement through an irradiation chamber having an ultraviolet light source at 90-375nm (preferably 300-350nm) having an irradiation density of 50-300 mW/cm 2 (preferably 150-250 mW/cm 2 )for a period of three to seven seconds is desired. Passage of a catheter through the chamber at a rate of 0.64 to 5.08 cm (0.25 to 2.0 inches)/second (1.27 cm to 2.54 cm or 0.5 to 1.0 inches/second) in a chamber having three to nine inches length is suitable. When using ionizing radiation, a radiation density of 1 to 100 kRads/cm 2 (preferably 20 to 50 kRads/cm 2 ) may be applied to the solution or suspension on the polymeric substrate.
- Exceptional durability of the resulting coating is produced by repetition of the dipping/solvent removal/irradiation steps up to five times. Preferred are two to four repetitions.
- FIG. 1 shows an infusion catheter (100) constructed according to one embodiment of the invention.
- the catheter (100) has an elongate tubular body (102) with proximal (104) and distal (106) ends and an open inner lumen (108) extending between the ends.
- the elongate tubular body (102) has three segments; a relatively flexible and strong distal segment (120), a relatively stiff tapered proximal segment (122) and a transition section or segment (124) between the proximal band distal segments that is less flexible than the distal segment (120) but more flexible than the proximal segment (122).
- the elongate tubular body (102) has a strong distal segment (120) which is desirably relatively flexible such that the catheter can easily navigate a tortuous vessel pathway.
- a force of about 4.5 x 10 -4 N (1 x 10 -4 pounds) corresponds to a deflection of the material that is 10° from horizontal, or only about 22.5 x 10 -4 N (5 x 10 -4 pounds) of force to deflect the material about 80° from horizontal.
- relatively strong is meant that the material has a burst pressure of greater than 13.5 bar (195 psi), more preferably, the burst pressure is between about 13.5 and 15.2 bar (195 and 220 psi).
- the flexible distal segment (120) has an open end which allows for the infusion of diagnostic, therapeutic, or vaso-occlusive agents into the target site.
- the flexible distal segment (120) preferably is made of a polymer that is springy and biologically compatible such as low density polyethylene, polyurethane, a block copolymer of polyamide, polyvinyl chloride, or silicone or blends of the above.
- the flexible distal segment (120) may carry one or more radiopaque bands (130) or may be doped with a radiopaque material such as barium sulfate, bismuth trioxide, bismuth carbonate, tungsten, tantalum or the like so that the location of the distal region of the catheter within the vessel may be visualized radiographically.
- the distal segment (120) typically makes up between about 5 and 25% of the total length of the tubular member and is between about 5 and 40 cm long, preferably between about 10 and 20 cm long.
- the inner diameter of the distal segment (120) may be between about 0.25 and 0.50 mm, more preferably between about 0.25 and 0.35 mm.
- the outer diameter of the distal segment may be between about 0.50 and 0.80 mm, more preferably between about 0.60 and 0.70 mm.
- the wall thickness of the distal segment 120 is between about 0.1 and 0.3 mm.
- the proximal segment (122) of the elongate tubular body (102), when used as a flow-directed infusion catheter, is relatively stiff such that it can be easily pushed thus eliminating the need for guidewire support.
- the proximal segment (122) may be made of a polymeric or metallic material that is relatively stiff and biologically compatible such as high density polyethylene, polypropylene, Nylon, polyurethane, polyimides, polyvinyl chloride, polysulfones, polyfluorocarbons, polyethylene terephthalate, their mixtures, copolymers; or polyester elastomers or a braided shaft (a polymer outer core with a metallic mesh inner core).
- the proximal segment (122) may comprise a tapered proximal section (134) for attachment to the proximal end fitting (150) and a distal section (132).
- the proximal section (134) of proximal segment (122) may make up between about 60% and 80% of the total length of the tubular member (102) and typically is between about 90 and 130 cm long, preferably between about 100 and 120 cm long.
- the largest inner diameter of the proximal section (134), measured at the proximal end (104) of the tubular member 102, is often between about 0.40 and 0.60 mm, more preferably between about 0.45 and 0.55 mm.
- the outer diameter of the proximal section (134) at the proximal end (104) of the tubular member (102) is between about 0.8 and 1.2 mm.
- the wall thickness of the proximal section (134) of proximal segment (122) is between about 0.1 and 0.4 mm, more preferably between about 0.2 and 0.3 mm.
- the distal section (132) of proximal segment (122) makes up between 10 and 20% of the total length of the tubular body (102) and is between about 20 and 40 cm long, preferably between about 20 and 30 cm long.
- the inner diameter of the distal section (132) of proximal segment (122) may be between about 0.20 and 0.50 mm, more preferably between about 0.25 and 0.35 mm.
- the outer diameter of the distal section (132) of proximal segment (122) is between about 0.60 and 0.90 mm, more preferably between about 0.60 and 0.70 mm.
- the wall thickness of the distal section (134) of proximal segment (122) is typically between about 0.1 and 0.3 mm.
- the transition section (124) of the elongate tubular body (102) is less stiff than the proximal segment (122) but more stiff than the distal segment (120).
- a suitable material that is biologically compatible is a polymer such as polyurethane, a block copolymer of polyamide, polyvinyl chloride or silicone with greater durometer reading (i.e. that is stiffer) than the flexible distal segment (120).
- the transition section (124) may be radiopaque and thus observable in the event that the catheter becomes lodged in a particular portion of the vasculature or buckles.
- the polymeric material may be doped with a radiopaque material such as barium sulfate, bismuth carbonate, bismuth trioxide, tungsten, tantalum or the like.
- the transition section (124) may make up between about 10 and 20% of the total length of the tubular member (102) and is between about 20 and 40 cm long, preferably between about 25 and 35 cm long.
- the transition section (124) may be of constant diameter or may be tapered.
- the inner diameter of the transition section (124) may be between about 0.20 and 0.50 mm, more preferably between about 0.20 and 0.35 mm.
- the outer diameter of the transition section (124) may be between about 0.50 and 0.90 mm, more preferably between about 0.60 and 0.70 mm.
- the wall thickness of the transition section (124) may be between about 0.1 and 0.3 mm.
- the proximal segment (122), transition section (124), and distal segment (120) are joined at junctions (140) and (142), respectively.
- the junctions may be formed by flaring, overlapping, and heat fusing the materials of the proximal segment (122) and transition section (124) and the transition section (124) and distal segment (120). Other methods for forming the junction, e.g., heat welding, solvent welding, etc. are also suitable.
- the distal segment (120), transition section (124) and distal section (132) of proximal segment (122) may all have approximately the same outside diameter or the transition section (124) and the distal section (132) of the proximal segment (122) may be tapered.
- a standard proximal end fitting (150) is attached to the proximal end (134) of the proximal segment (122) often by heat fusion with reinforcing tubing.
- FIG. 2 shows an embodiment of the distal segment (120) of the catheter where the tip (160) of the catheter is pre-shaped by heating with steam so that the distal end (106) points towards the wall of the vessel rather than in the direction of blood flow to increase the ease of manipulation through the tortuous vessel pathway.
- the particular embodiment shown is an "S" shape, but the tip may be any shape that allows for access to the particular vasculature being treated.
- One additional shape is that of a hockey stick. In this way, if the catheter becomes lodged against the vessel wall, the infusion of liquid through the catheter propels the distal end (106) of the catheter away from the vessel wall. Since the stiff proximal segment (122) is pushed, the distal segment (120) will be carried by the blood flood to the target site.
- the catheter described above is useful in delivering diagnostic, therapeutic, or vaso-occlusive agents and devices to deep tissue, usually without need for a guidewire.
- FIG. 3 shows a catheter assembly (200) for placing the infusion catheter (100) at the target site.
- An appropriate guiding catheter (202) is inserted into the vasculature using standard placement techniques.
- a rotating hemostatic valve (204) may be utilized by connection to the guiding catheter luer adapter (206).
- the guiding catheter (202) is continuously flushed with saline.
- the thumb-screw of the valve (204) is opened and the infusion catheter (100) is inserted through the rotating hemostatic valve (204).
- a Teflon-coated stainless steel stylet (208) is first inserted into the flow-directed infusion catheter (100) in order to prevent kinking of the infusion catheter (100) within the valve (204).
- the distal end (106) of the infusion catheter (100) is advanced proximal to the tip of the guiding catheter (202).
- the stylet (208) is then removed from the infusion catheter (100). Once the stylet (208) is removed, the infusion catheter (100) is pushed out of the guiding catheter (202).
- the flow-directed infusion catheter (100) is gently guided by the flow of blood in the vasculature to the target site.
- gentle pushing and pulling and injection of saline or contrast medium through the catheter lumen (108) may aid in the placement of the catheter at the target site.
- Such agents may include radiopaque agents for viewing blood vessel anatomy and blood flow characteristics in the target region, vaso-occlusive agents which can be used to produce small-artery vaso-occlusion in the tissue region supplied by the target vessel, and pharmacological agents, such as anti-tumor drugs or sclerosing agents such as alcohols, which are effective against identified disease states at the target site.
- Vaso-occlusive agents useful in the treatment of arteriovenous malformations include polymers that are activated in the presence of polar solvents such as water and include materials such as n-butylcyanoacrylate.
- vaso-occlusive agents useful in the treatment of arteriovenous malformations include polymer solutions that coagulate by diffusion of the solvent when in contact with blood. Polyvinyl acetate dissolved in dimethylsulfoxide is one such agent.
- vaso-occlusive coils may be injected into the infusion catheter and delivered to a target site to occlude the blood flow at that site.
- Figure 4 shows a variation of the invention in which the catheter is guided to its intended site by the use of a guidewire rather than through the use of blood flow.
- the catheter assembly (400) includes an elongate member (402) having a proximal end (404) and a distal end (406) and an inner lumen which extends between those two ends.
- the elongate tubular body (402) has three segments; a relatively flexible distal segment (408), a relatively stiff proximal segment (410) and a transition section or middle segment (412) (separated at junction (414) from the proximal segment) between the proximal and distal segments that is less flexible than the distal segment (408) but more flexible than the proximal segment (410).
- guidewire (414) often having a bent tip (416) to allow ease of passage through the vasculature.
- a catheter will have a small radiopaque band (418) of gold, platinum, palladium, or the like to permit monitoring of the catheter tip's position in relation to the tip of the guidewire or, when the guidewire is not in the catheter, to the vasculature itself.
- a standard proximal end fitting (420) may attached to the proximal end (404) of the proximal segment (410) often by heat fusion with reinforcing tubing. As is described in U.S. Pat. No.
- the variation of flexibility may be introduced into the catheter assembly by use of sections of discrete coaxial tubing, e.g., by use of an inner stiff tube of polypropylene or high density polyethylene covered by a flexible tube of low density polyethylene or silicone in the proximal section (410) with the inner tubing junction found at (410).
- a thinner wall inner tubing of the same polymer as found in the proximal section (410) may be used as the inner tubing in middle section (412) to provide decreased stiffness in the middle section (412).
- the outer coaxial layer could be of the same composition and dimensions from proximal end (404) to distal end (406).
- the catheters had three discrete sections: A proximal section of low-density polyethylene laminated over polypropylene tubing (having 0,559mm (0.022") I.D. and 0,991 mm (0.039") O.D.) of 115 cm. length, a transition section of low density polyethylene laminated over polypropylene tubing (having 0,559 mm (0.022”) I.D. and 0,991 mm (0.036”) O.D.) of 15 cm., and a distal section of low density polyethylene of 20 cm.
- the low density polyethylene outer covering was a single piece covering throughout the length of the catheters.
- the inventive catheter coating was produced using the following procedure:
- the comparative silicone catheter coating was applied using the following procedure:
- the catheters were separately introduced into a USCI Angiographic Systems Berenstein J-tip guiding catheter in a test rig allowing measurement of the force needed to push and to pull the catheters through the guiding catheter.
- Each of the catheters was tested through 20 pulls and pushes of 2 inches pushed and pulled at a rate of 2.54 cm (1 inch)/minute. In this way both absolute force needed to introduce the catheter may be recorded as well as the magnitude of all deterioration in the slipperiness.
- the measurements were taken for both the midsection and for the distal sections of the two catheters. MIDSECTION Pull. No.
- Comparative Invention 1 0.198 (0.044) 0.112 (0.025) 20 0.243 (0.054) 0.112 (0.025) DISTAL SECTION Pull. No. Comparative Invention 1 0.104 (0.023) 0.058 (0.013) 20 0.122 (0.027) 0.058 (0.013)
Abstract
Description
characterised in that at least the distal segment has a lubricious coating comprising two or more polymers formed from, or a copolymer of, at least two monomers from N-vinylpyrrolidone, acrylamide or polyethylene glycol acrylate monomers and/or a polymer or copolymer comprising acrylamidomethylpropane sulfonic acid and its salts.
MIDSECTION | ||
Pull. No. | Force, N(lbs.) | |
Comparative | Invention | |
1 | 0.198 (0.044) | 0.112 (0.025) |
20 | 0.243 (0.054) | 0.112 (0.025) |
DISTAL SECTION | ||
Pull. No. | Comparative | Invention |
1 | 0.104 (0.023) | 0.058 (0.013) |
20 | 0.122 (0.027) | 0.058 (0.013) |
Claims (15)
- A catheter assembly comprising an elongated tubular (102, 402) member having proximal and distal (104, 106, 404, 406) ends and an inner lumen (108) extending between these ends, the member comprising:(a) a relatively stiff proximal segment (122, 410);(b) a relatively flexible distal segment (120, 408); and(c) a transition section (124, 412) between the proximal and distal segments that is less flexible than the distal segment but more flexible than the proximal segment;
characterized in that at least the distal segment has a lubricious coating comprising two or more polymers formed from, or a copolymer of, at least two monomers from N-vinylpyrrolidone, acrylamide or polyethylene glycol acrylate monomers and/or a polymer or copolymer comprising acrylamidomethylpropane sulfonic acid and its salts. - A catheter according to claim 1 wherein the distal segment (120, 408) and the transition section (124, 412) are both coated with a lubricious coating.
- A catheter according to claim 1 or 2 wherein at least a portion of the proximal segment (122, 412) is also coated with a lubricious coating.
- A catheter according to claim 3 in which the polyethylene glycol acrylate is a mono-alkoxy polyethylene glycol mono(meth)acrylate.
- A catheter according to claim 4 wherein the mono(meth)acrylate comprises mono-methoxy triethylene glycol mono(meth)acrylate, mono-methoxy tetraethylene glycol mono(meth)acrylate or polyethylene glycol mono(meth)acrylate.
- A catheter according to any of claims 1 to 3 wherein the lubricious coating is of a copolymer of polyvinylpyrrolidone and polyacrylamide.
- A catheter according to any preceding claim wherein the distal segment (120, 408) has a burst pressure of at least about 13.5 bar (195 psi) and is made of a material which will show a force of about 4.5 x 10-4N (10-4 pounds) or less when ten centimetres of the material is deflected 10° from horizontal.
- A catheter according to claim 7 wherein the burst pressure of the distal segment (120, 408) is between about 13.5 to 15.2 bar (195 to 220 psi).
- A catheter according to claim 7 wherein the distal segment (120,408) is made of a material that further will show an additional force of about 4.5 x 10-5N (10-5 pounds) or less for each 1° of deflection of the material from horizontal.
- A catheter according to any preceding claim wherein the proximal segment (122, 410) is made of a polymeric material which is polyethylene, polypropylene, nylon, polyvinyl chloride, polyethylene terephthalate or other polyester elastomer and/or a polymer outer core with a metallic mesh inner core and laminates thereof.
- A catheter according to any preceding claim wherein the distal segment (120, 408) is made of a polymeric material which is polyethylene, polypropylene, polyurethane, a block copolymer of polyamide, polyvinyl chloride, silicone and/or a blend thereof.
- A catheter according to claim 11 wherein the polymeric material of the distal segment (120, 408) is doped with a metallic material which is barium sulfate, bismuth trioxide, bismuth carbonate, tungsten and/or tantalum.
- A catheter according to any preceding claim wherein the transition section (124, 412) is made of a polymeric material which is polyethylene, polypropylene, polyurethane, a block copolymer of polyamide, polyvinyl chloride and/or silicone or a laminate thereof.
- A catheter according to claim 13 wherein the polymeric material of the transition section (124, 412) is doped with a metallic material which is barium sulfate, bismuth trioxide, bismuth carbonate, tungsten and/or tantalum.
- A catheter according to any preceding claim wherein the distal segment (120, 408) is in an S-shaped or hockey stick-shaped configuration.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/060,401 US5531715A (en) | 1993-05-12 | 1993-05-12 | Lubricious catheters |
US60401 | 1993-05-12 | ||
PCT/US1994/005343 WO1994026336A1 (en) | 1993-05-12 | 1994-05-12 | Lubricious catheters |
Publications (3)
Publication Number | Publication Date |
---|---|
EP0693948A4 EP0693948A4 (en) | 1995-12-07 |
EP0693948A1 EP0693948A1 (en) | 1996-01-31 |
EP0693948B1 true EP0693948B1 (en) | 1998-07-22 |
Family
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Family Applications (1)
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EP94916763A Expired - Lifetime EP0693948B1 (en) | 1993-05-12 | 1994-05-12 | Lubricious catheters |
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US (4) | US5531715A (en) |
EP (1) | EP0693948B1 (en) |
JP (1) | JP2705852B2 (en) |
AT (1) | ATE168568T1 (en) |
AU (1) | AU680911B2 (en) |
CA (1) | CA2127257C (en) |
DE (1) | DE69411903T2 (en) |
IL (1) | IL109637A0 (en) |
TW (1) | TW275586B (en) |
WO (1) | WO1994026336A1 (en) |
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US6706025B2 (en) | 2004-03-16 |
US5789018A (en) | 1998-08-04 |
WO1994026336A1 (en) | 1994-11-24 |
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JPH07504599A (en) | 1995-05-25 |
DE69411903D1 (en) | 1998-08-27 |
AU6832894A (en) | 1994-12-12 |
CA2127257C (en) | 2002-04-23 |
JP2705852B2 (en) | 1998-01-28 |
US6221061B1 (en) | 2001-04-24 |
IL109637A0 (en) | 1994-08-26 |
CA2127257A1 (en) | 1994-11-13 |
TW275586B (en) | 1996-05-11 |
DE69411903T2 (en) | 1999-04-01 |
US20010011165A1 (en) | 2001-08-02 |
EP0693948A4 (en) | 1995-12-07 |
EP0693948A1 (en) | 1996-01-31 |
US5531715A (en) | 1996-07-02 |
ATE168568T1 (en) | 1998-08-15 |
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